Dynamic Biometric Mesh

ABSTRACT

A dynamic biometric mesh ( 10 ) has a plurality of radial members ( 30 ) and a plurality of catenaries ( 20 ). Each catenary ( 20 ) extends between and is fixed to at least one pair of adjacent radial members ( 30 ). The plurality of catenaries ( 20 ) and radial members ( 30 ) form a low mass structural system arranged in an architecture configured to be structurally stable in tension and pliable for deployment and integration with biologic tissue.

TECHNICAL FIELD

The present invention relates to meshes for supporting tissuesgenerally, more particularly, a mesh for hernia repair or breastsupport.

BACKGROUND OF THE INVENTION

Ventral abdominal hernias are common and associated with significantmorbidity. The most common cause for ventral hernias remains previousopen abdominal surgery, although prolapse via epigastric and lowerabdominal muscle wall are common as well. Over 100,000 ventral herniarepairs are performed in the USA annually. Untreated abdominal herniascan result in incarceration of bowel; organ prolapse; bowel obstruction;strangulation of bowel; and even death.

Rising obesity rates have resulted in increased recurrence rates ofventral hernias reported as high as 11% following open abdominalsurgical procedures

Long-term prospective studies have established mesh repair of ventralhernia as superior to primary suture repair. As noted by Dr. S.Saureland, the incidence of recurrent herniation is 10-fold higher withdirect repair compared to a mesh prosthesis

Existing prosthetic meshes are associated with a range of problems aswell, including significant recurrent rates (10-30%); fibrosis; chronicpain; stiffness of the abdominal wall; intestinal fistula; infection;recurrences; anchor point failures; thromboses; calcification; andunfavorable bowel interactions.

Existing ventral hernia mesh technologies are biased in design as staticload bearing systems, and fail to account for tensional integrity, ortensegrity; a model more appropriate to biologic systems. The preferencefor stiff and static meshes arises from the belief that flexible meshesare prone to resulting in abdominal bulges following herniorrhaphy;however, stiff meshes fail to dissipate tensile forces across theabdominal wall and instead absorb these energies which may contribute totheir ultimate failure particularly at the anchoring points.Furthermore, many meshes are composed of non-biocompatible materials andthus destined for encapsulation that promote chronic inflammatoryresponses at the implantation site. Many current mesh designs rely on alarge mass of material resulting in thick scar formation which in turnleads to stiffness of the abdominal wall and chronic pain. Finally, nocurrent mesh is manufactured to match the hernia defect with regard tosize, mechanical profile, or consider integrating dynamic tensileproperty during the healing process.

The present invention disclosed herein provides a novel ventralabdominal mesh designed to address problems associated with ventralhernias that integrate the principles of tensegrity, biocompatibility,and biometric customization.

SUMMARY OF THE INVENTION

A dynamic biometric mesh has a plurality of radial members and aplurality of catenaries. Each catenary extends between and is fixed toat least one pair of adjacent radial members. The plurality ofcatenaries and radial members form a low mass structural system arrangedin an architecture configured to be structurally stable in tension andpliable for deployment and integration with biologic tissue.

Biometric mesh further has a central region or opening from which theradial members extend outwardly to ends defining an outer perimeter. Theplurality of catenaries are preferably arranged in circumferentialextending rows spaced along lengths of the radial members. Adjacentcircumferential extending rows are more closely spaced near the centerregion and increase in spacing towards the outer perimeter.

The dynamic biometric mesh of the invention has the plurality ofcatenaries fixed to radial members and the sag or hang between theradial members in the rage from 0, a straight line, or greater than 0evidencing a curved hanging path. Each catenary has zero tension in aflat plane when formed as a mesh. The dynamic biometric mesh of at leastone embodiment has one or more catenaries with a positive sag or hang(a), (a) being a drop or sag between a straight line passing through thefixed ends at the radial member. Preferably all of the catenaries areelastic having a defined stretch under tension. Similarly it ispreferred that the radial members are elastic having a defined stretchunder tension.

Ideally, the dynamic biometric mesh is conformable about a convexcurvature. The dynamic biometric mesh has the outer perimeter having aplurality of attachment or anchoring points to attach the mesh totissue. The mesh can be stretched to the attachment points topre-tension the mesh along the attachments. The pre-tensioning of themesh places a tension on the catenaries and wherein the catenariesachieve a tensioned equilibrium after the mesh is anchored or affixed tothe tissue. The catenaries stretch under expansion or retract undercontraction in relation to the movement of the tissue to which the meshis affixed. In one embodiment, the dynamic biometric mesh has anasymmetric configuration having an upper hemisphere extending above thecentral opening of increased elasticity or stretch and a lowerhemisphere having a reduced elasticity or stretch. The lower hemispherehas a plurality of struts, each strut extending diagonally betweenadjacent catenaries and adjacent radial members. The struts arepreferably attached to intersections of a respective catenary and radialmembers. The struts of the lower hemisphere are positioned diagonally ateach intersection and can be selectively removed by cutting one or morestruts to tune the structure of the mesh to accommodate the tissue towhich the mesh is attached.

The dynamic biometric mesh allows for at least an upper portion orhemisphere of the mesh to expand under tension at least to 150% from itsas formed unattached structure. The radial members and the catenarieshave the same elasticity. The struts, radial members and catenaries mayhave the same elasticity.

The dynamic biometric mesh of another embodiment has one or more of theplurality of catenaries formed as a shelf having a width (w) and alength (1) creating top and bottom surface areas to affix biologicalmaterials, chemicals or pharmaceuticals to enhance tissue integration.The dynamic biometric mesh can be formed by weaving monofilaments in amulti-ply configuration. The dynamic biometric mesh is a three plyconfiguration. Preferably, the dynamic biometric mesh can be amulti-tiered structure having two or more connected layers of mesh.

The dynamic biometric mesh redirects forces from lateral tension intorostral-caudal alignment to direct reconstitution and normalize tissuerepair. The dynamic biometric mesh, as designed, distributes tensionacross the catenaries and radial members to dissipate dynamic forces atthe anchoring points. The dynamic biometric mesh can be configured forattachment to an abdominal wall for use in repair of abdominal wallhernias or to provide dynamic stabilization and support of breasttissue. The dynamic biometric mesh can be degradably defined by thematerial composition to be selectively absorbed or biologicallyintegrated into the tissue to which it is attached. The dynamicbiometric mesh can be formed using one or more techniques such as cast,printed, corrugated, embossed, extruded, die cut, welded, laser etched,laser modified tissue mimetic biodynamic.

The dynamic biometric mesh can have random or preferred surfaceorientation and roughness. The dynamic biometric mesh can be made withintrinsic cell instruction properties engineered into fibers which makeup the catenaries and radial members using laser etching. The cellinstruction properties of the mesh promote incorporation of the meshinto surrounding tissues by promoting tissue ingrowth. Alternatively, orin combination with the cell instruction, the dynamic biometric mesh mayalso include metal salts which are incorporated into fiber of thecatenaries and radial members to act as competitive inhibitors tomediators of inflammatory response. These metal salts include titaniumdioxide as a competitive inhibitor of metalloprotease mediators of theinflammatory response. The dynamic biometric mesh can be conditionedwith autologous mesenchymal stem cells (MSCs) derived from processedadipose tissue, and consistent with the stromal vascular fraction (SVF).The mesh can be conditioned with the MSCs in a bioreactor in advance ofinsertion into the hernia defect. The dynamic biometric mesh can includea matrix to enhance cell attachment, stimulate differentiation andaccentuate force transduction in alignment of the cell orientation. Thedynamic biometric mesh preferably is a biosynthetic composite structurecustomized to the subject and accelerates incorporation into adjacenttissues. The dynamic biometric mesh can be manufactured using a 3-Dprinting technology, wherein the mesh is made on demand and to preciselymatch the hernia defect in the subject based on non-invasivemeasurements including physical examination. The dynamic biometric meshis formed as a broad platform of uniform isotropic distributed radialmembers and catenaries or struts formed by either printed, laser cut,die cut, embossed, sprayed on suitable differential electrodes to aligncharge, or other means. The catenaries, radial members or struts can beover sprayed with collagen, PGLA, PCL, Poly-imides, or otherbio-absorbable polymers. The dynamic biometric mesh, in one or moreembodiments, emulates zoomorphic design, specifically that of a spiderweb, and is intended to possess an open architecture thus reducinginfection and inflammation. The dynamic biometric mesh has the stress orelongation characteristics of the mesh to be suited to accommodating thecyclical load bearing properties of the ventral abdominal wall and theinterstices of the mesh are smaller than 12 mm or less. The dynamicbiometric mesh may incorporate one or more features in cross section ofa woody stem, of a plant branching interface, demonstrates regular andrandomized cells, Fibonacci and ordered arrays, varying diameters andregular, ordered arrays of inner cells any of which imparting structuraltension to lateral distortion without imposing material stiffness. Thecatenaries and radial members are preferably formed as fibers having atensile strength in the range of 50 to 150 N/m, preferably about 100N/m. The catenaries and radial members may have a fiber diameter of 0.2mm or greater, preferably a fiber diameter of 0.26 mm. The dynamicbiometric mesh preferably has the Young's modulus of component fibersbeing 34 GPa or greater. The suture pull out strength is at least 5.5 kgat the outer perimeter of the mesh.

BRIEF DESCRIPTION OF THE DRAWINGS

The invention will be described by way of example and with reference tothe accompanying drawings in which:

FIG. 1A is a reduced mass mesh made in accordance with a firstembodiment of the invention.

FIG. 1B is the same mesh as FIG. 1A wherein the catenaries are curved,each being suspended between two points on pairs of radial members.

FIG. 2 is a second embodiment mesh with stiffening struts.

FIG. 3 is a third embodiment with an alternative mesh design.

FIG. 4 is a fourth embodiment alternative mesh design.

FIG. 5 is a multi-layered mesh.

FIG. 6 is a depiction of the mesh on a convex surface.

FIGS. 7A and 7B are a fifth embodiment mesh for use in breast surgery asa breast support structure.

DETAILED DESCRIPTION OF THE INVENTION

The present invention employs a plurality of catenary members or fibershereinafter called catenaries.

In physics and geometry, a catenary is the curve that an idealizedhanging chain or cable assumes under its own weight when supported onlyat its ends. The curve has a U-like shape, superficially similar inappearance to a parabola, but it is not a parabola: it is a (scaled,rotated) graph of the hyperbolic cosine. The curve appears in the designof certain types of arches and as a cross section of the catenoid—theshape assumed by a soap film bounded by two parallel circular rings.

The catenary is also called the “alysoid”, “chainette”, or, particularlyin the material sciences, “funicular”.

Mathematically, the catenary curve is the graph of the hyperbolic cosinefunction. The surface of revolution of the catenary curve, the catenoid,is a minimal surface, specifically a minimal surface of revolution. Themathematical properties of the catenary curve were first studied byRobert Hooke in the 1670's, and its equation was derived by Leibniz,Huygens and Johann Bernoulli in 1691.

Catenaries and related curves are used in architecture and engineering,in the design of bridges and arches, so that forces do not result inbending moments.

Over any horizontal interval, the ratio of the area under the catenaryto its length equals a, independent of the interval selected. Thecatenary is the only plane curve other than a horizontal line with thisproperty. Also, the geometric centroid of the area under a stretch ofcatenary is the midpoint of the perpendicular segment connecting thecentroid of the curve itself and the x-axis.

In an elastic catenary, the chain is replaced by a spring which canstretch in response to tension. The spring is assumed to stretch inaccordance with Hooke's Law. Specifically, if p is the natural length ofa section of spring, then the length of the spring with tension Tapplied has length

${s = {\left( {1 + \frac{T}{E}} \right)p}},$

where E is a constant. In the catenary the value of T is variable, butratio remains valid at a local level, so

$\frac{s}{p} = {1 + {\frac{T}{E}.}}$

The curve followed by an elastic spring can now be derived following asimilar method as for the inelastic spring.

The equations for tension of the spring are T cos φ=T₀, and T sinφ=λ₀gp, from which

${\frac{y}{x} = {{\tan \; \phi} = \frac{\lambda_{0}\; p}{T_{0}}}},{T = \sqrt{T_{0}^{2} + {\lambda_{0}^{2}^{2}p^{2\;}}}},$

where p is the natural length of the segment from c to r and λ₀ is themass per unit length of the spring with no tension and g is theacceleration of gravity. Write

${a = {{\frac{T_{0}}{\lambda_{0}}\mspace{14mu} {so}\mspace{14mu} \frac{y}{x}} = {{\tan \; \phi} = \frac{p}{a}}}},{T = {\frac{T_{0}}{a}{\sqrt{a^{2} + p^{2}}.}}}$

Then

${\frac{x}{s} = {{\cos \; \phi} = {{\frac{T_{0}}{T}\mspace{14mu} {and}\mspace{14mu} \frac{y}{s}} = {{\sin \; \phi} = \frac{\lambda_{0}\; p}{T}}}}},$

from which

$\frac{x}{p} = {{\frac{T_{0}}{T}\frac{s}{p}} = {{T_{0}\left( {\frac{1}{T} + \frac{1}{E}} \right)} = {\frac{a}{\sqrt{a^{2} + p^{2}}} + {\frac{T_{0}}{E}\mspace{14mu} {and}}}}}$$\frac{y}{p} = {{\frac{\lambda_{0}\; p}{T}\frac{s}{p}} = {{\frac{T_{0}p}{a}\left( {\frac{1}{T} + \frac{1}{E}} \right)} = {\frac{p}{\sqrt{a^{2} + p^{2}}} + {\frac{T_{0}p}{Ea}.}}}}$

Integrating gives the parametric equations

${x = {{a\; {{arcsinh}\left( {p/a} \right)}} + {\frac{T_{0}}{E}p} + \alpha}},{y = {\sqrt{a^{2} + p^{2}} + {\frac{T_{0}}{2{Ea}}p^{2}} + {\beta.}}}$

Again, the x and y-axes can be shifted so α and β can be taken to be 0.So

${x = {{a\; {{arcsinh}\left( {p/a} \right)}} + {\frac{T_{0}}{E}p}}},{y = {\sqrt{a^{2} + p^{2}} + {\frac{T_{0}}{2{Ea}}p^{2}}}}$

are parametric equations for the curve.

Chain under a general force: With no assumptions have been maderegarding the force G acting on the chain, the following analysis can bemade.

First, let T=T(s) be the force of tension as a function of s. The chainis flexible so it can only exert a force parallel to itself. Sincetension is defined as the force that the chain exerts on itself, T mustbe parallel to the chain. In other words, T=Tu, where T is the magnitudeof T and u is the unit tangent vector.

Second, let G=G(s) be the external force per unit length acting on asmall segment of a chain as a function of s. The forces acting on thesegment of the chain between s and s+Δs are the force of tension T(s+Δs)at one end of the segment, the nearly opposite force −T(s) at the otherend, and the external force acting on the segment which is approximatelyGΔs. These forces must balance so T(s+Δs)−T(s)+GΔs≈0. Divide by Δs andtake the limit as Δs→0 to obtain

${\frac{T}{s} + G} = 0.$

These equations can be used as the starting point in the analysis of aflexible chain acting under any external force. In the case of thestandard catenary, G=(0, −λg) where the chain has mass λ per unit lengthand g is the acceleration of gravity.

In the present invention, each catenary can have or exhibit a linearpath connected at two fixed points on the pair of radially adjacentmembers. In this case, the catenary is not curved, but its elasticitytransmits the tension forces along the stretched path parallel to thecatenary. Exactly as found mathematically above. Interestingly, theelastic or curved catenary system is an ideal structure for affixing toa three dimensional surface like a sphere or any convex shape as itconforms elegantly about the curvature. Ideally, the curved catenarieshave a smaller hang at the origin and increase in hang at the radialextremes. This allows for the increased expansion outward of theconvexity prior to tensioning the mesh system. When affixed or anchoredto the tissue, the radial members and catenaries can be tensioned andthe tension will be parallel to the member's path and redirected alongattached catenaries.

Biologic systems have a component of load bearing and tensionalintegrity or tensegrity. Many static structures designed to repair orreplace biologic structures are purely load bearing in nature andtherefore destined to fail as they cannot replicate the varying tensionsthe abdominal wall cycles through thousands of time daily. For example,the Law of Laplace predicts abdominal wall tension is a dependentvariable of abdominal wall radius. The radius of the abdomen varies manytimes daily with breathing, coughing, and locomotion resulting invarying abdominal wall tensions. In fact, it has been reported that theventral abdominal fascia elongates up to 150% of resting length duringexercise. As such, the ventral abdominal wall cannot therefore betreated as a static structure in which a defect can be repaired with astatic mesh.

Tissue incompatibility results from the lack of incorporation intoadjacent tissues of current prostheses. Since the prosthesis cannot beincorporated, a foreign body reaction results and leads to encapsulationby fibrous tissue as the body attempts to sequester the foreignmaterial. While fibrous tissue effectively separates and hides thetissue, the inter-fragmentary strain of dissimilar tissues results inchronic irritation, fibrous proliferation and sustained inflammation.Under this biologic strain, the capsule in turn can harbor bacteriaresulting in chronic infections and inflammatory response.

Biometric analysis of abdominal wall defects currently documents thedefect in 2-dimensions, chiefly with imaging and physical exam. Theshortcoming does not take into account differential abdominal walltensions that vary between the separate anatomic zones of the abdominalwall. For instance, none of the current models recognize that the lowerabdomen generates greater tension in comparison with the upper abdomen.Taking into consideration differential abdominal wall tensions, extanttechnologies can potentially integrate anatomic distinctions ofindividual patients and offer insight into biomechanics thus permittingthe design of customized meshes from basic stock designs.

Current hernia meshes are non-customized prosthetic devices. The presentinvention allows a customized prosthesis to be fabricated based onbiometric analysis of the subject.

Anchor point failures are a common cause for hernia failures. Mostanchoring techniques in open hernia failure rely on horizontally appliedsutures which necessarily cause tissue strangulation and ischemia. Theischemic tissue results in loosening of the anchoring sutures andfailure of the fixation point. The current mesh design may be anchoredusing traditional suture techniques or even more advanced fixationtechniques.

Meshes composed of acellular dermal matrix (ADM) are purported to resultin tissue regeneration but suffer rapid decline of tensile strengthwhich fails to account for efficacy in herniorrhaphy. Furthermore, ADMsprobably do not undergo the degree of tissue incorporation andneo-vascularization envisioned by manufacturers/vendors.

As shown in FIGS. 1-7, the proposed mesh 10 is engineered with intrinsicelastomeric properties and comprised of a system of catenaries 20 andtrusses or radial members 30, that might be additive, channeled, cast,printed, corrugated, embossed, extruded, die cut, welded, laser etched,laser modified, mimetic in origin, biodynamic, and incorporate randomand preferred surface orientation and roughness intended to actuate andamplify defined stresses within a range of tensile and compressiveforces that are known to be structurally stable in tension and yetsufficiently pliable for deployment and integration of biologic tissues;particularly those of the abdominal wall. Biometric mesh 10 further hasa central region or opening 12 from which the radial members 30 extendoutwardly to ends defining an outer perimeter 14. The arrangement ofcomponents serves to distribute tension across the hernia defect as wellas to dissipate dynamic forces to the anchoring points 40. The additionof struts 50, shown in FIGS. 2-4, to select areas of the mesh 10 canadjust the tensile properties of the prostheses to better accommodatethe native tensile properties of the implant site. The mesh 10 can becomposed of separate and numerous layers that are connected andjuxtaposed to inhibit strain and protect the structural integrity, asshown in FIG. 5. In preferred embodiment, forces will be redirected fromlateral tension into rostral-caudal alignment to direct reconstitutionand normalize anatomical repair of the linea alba,

Elastomeric properties of the mesh 10 can be engineered into the mesh 10as result of weaving static monofilament materials in a three-plyconfiguration. Use of monofilament materials reduce the intersticesavailable for seeding with bacterial contaminants.

Intrinsic cell instruction properties can be engineered into the meshfibers using laser etching. The cell instruction properties of the meshpromotes incorporation of the prostheses into surrounding tissues bypromoting tissue ingrowth.

Metal salts incorporated into the mesh fiber act as competitiveinhibitors to mediators of inflammatory response. These could includetitanium dioxide as a competitive inhibitor of metalloprotease mediatorsof the inflammatory response (Spyros AS, 2013).

In one instance, the proposed mesh 10 is conditioned with autologousmesenchymal stem cells (MSCs) derived from processed adipose tissue, andconsistent with the stromal vascular fraction (SVF).

The mesh 10 is preferably conditioned with the MSCs in a bioreactor inadvance of insertion into the hernia defect. It is well known in the artthat matrix coating enhances cell attachment, stimulates differentiate,and accentuates force transduction in alignment of the cell orientation.The biosynthetic composite structure can be customized to the subjectand accelerates incorporation into adjacent tissues. It is envisionedthat the mesh 10 will ultimately be incorporated by organized tissuealigned and modeled with the tensile forces that the mesh is continuallysubject to. Conditioning of the mesh 10 with MSC will reduce fibrosisand potentially decrease bowel interactions such as adhesions.

The mesh 10 can be manufactured using a 3-D printing technology and cantherefore be made on demand and to precisely match the hernia defect inthe subject based on non-invasive measurements including physical exam.

In addition to a process of additive fabrication (3D-Printing), it isalso conceivable that a broad platform of uniform isotropic distributedstruts and trusses would be printed, laser cut, die cut, embossed,sprayed on suitable differential electrodes to align charge, or othermeans with these as example.

The struts 50 might also be over sprayed with collagen, PGLA, PCL,Poly-imides, or other bio-absorbable polymers known in the art.

Among other defined structures, the mesh 10 emulates zoomorphic design,specifically that of a spider web, and is intended to possess an openarchitecture thus reducing infection and inflammation. In this manner areduced-mass mesh 10 results. The stress/elongation characteristics ofwoven spider silk are particularly well suited to accommodating thecyclical load bearing properties of the ventral abdominal wall. Smallpore size is associated with increased rates of infection. Theinterstices of the proposed mesh are smaller than 12 mm or less than theminimal reported size for a Richter's hernia.

Still other biomimetic designs would include those elaborated in crosssection of woody stems, of plant branching interfaces, demonstratingregular and randominzed cells, fibonacci and ordered arrays, varyingdiameters and regular, ordered arrays of inner cells that impartstructural tension to lateral distortion without imposing materialstiffness.

Other potential elaborations of the design might be defined asmathematical roulette curves of the variety technically known ashypotrochoids and epitrochoids (similar to spirograph; images/figures atthe end. Example of such alternative designs are found in FIGS. 2-4.

As shown in FIG. 1, some of the catenaries 20 may be formed as shelves20S or trays 20 with surface undulations, mimetic grooves, instructiveand resonant surface effects can be incorporated into the mesh 10 atregular intervals in order to provide a purchase for MSCs and to serveas an initial nidus from where proliferation can occur to seed theentirety of the mesh 10. It is not believed that a confluence of cellmatrix is necessary prior to implantation, and disclose that the woundmilieu, including growth factors, stem cells, cytokines, andinflammatory priming are all possible events. Accentuating the potentialto define matrix deposition as an adjunct resonating dynamic integrationof loading bears the dividend of design.

The tensile strength of the mesh fibers is preferably between 50 and 150N/m, preferably about 100 N/m. The maximum tension generated across theabdominal wall is reported to be 32 N/m

Fiber diameter is 0.2 mm or greater, typically about 0.26 mm.

Young's modulus of component fibers is anticipated to be 34 GPa.

Suture pull out strength is at least 5.5 kg at the periphery orperimeter 14 of the mesh 10 at the anchor points 40.

As shown in FIG. 6, the dynamic mesh 10 is shown overlying a convexsurface 3 replicating an abdomen having a typical rounded or domedcurvature. As shown, the mesh 10 will conform easily to this surface,and does so with little or no effort due to its compliant nature. Thisis not possible with woven screen like mesh.

In FIGS. 7A and 7B, an alternative mesh 10 is shown. The mesh 10 isideally suited to support a patient's 2 breast 4 by being affixed to thelower portion of the tissue. As shown, the mesh 10 is made having halfthe structure of a hernia mesh 10, preferably the lower portion or lowerhemisphere. Alternatively, this construct can be achieved by folding themesh 10 of any of the previous figures to create a double layer of mesh.

The mesh 10 is best applied to reconstruct the inferior, or lower, poleof the breast 4. In this position, it can support an implant or nativebreast tissue thus opposing gravitational descent of an implant orbreast tissue. When the implant 10 is placed in the sub-pectoral plane,as is popular in breast reconstruction or augmentation, the tensegritystructure allows the implant 10 to migrate with activation of thepectoralis muscle 8 but the implant 10 would “spring” back when thepectoralis 8 is relaxed.

Variations in the present invention are possible in light of thedescription of it provided herein. While certain representativeembodiments and details have been shown for the purpose of illustratingthe subject invention, it will be apparent to those skilled in this artthat various changes and modifications can be made therein withoutdeparting from the scope of the subject invention. It is, therefore, tobe understood that changes can be made in the particular embodimentsdescribed, which will be within the full intended scope of the inventionas defined by the following appended claims.

What is claimed is:
 1. A dynamic biometric mesh comprises: a pluralityof radial members; a plurality of catenaries, each catenary extendingbetween and fixed to at least one pair of adjacent radial members; andwherein the plurality of catenaries and radial members form a low massstructural system arranged in an architecture configured to bestructurally stable in tension and pliable for deployment andintegration with biologic tissue.
 2. The dynamic biometric mesh of claim1 further comprises: a central region or opening from which the radialmembers extend outwardly to ends defining an outer perimeter; andwherein the plurality of catenaries are arranged in circumferentialextending rows spaced along lengths of the radial members.
 3. Thedynamic biometric mesh of claim 2 wherein adjacent circumferentialextending rows are more closely spaced near the center region andincrease in spacing towards the outer perimeter.
 4. The dynamicbiometric mesh of claim 1 wherein the plurality of catenaries are fixedto radial members and the sag or hang between the radial members in therage from 0, a straight line, or greater than 0 evidencing a curvedhanging path, each catenary having zero tension in a flat plane whenformed as a mesh.
 5. The dynamic biometric mesh of claim 1 wherein oneor more catenaries has a positive sag or hang (a), (a) being a drop orsag between a straight line passing through the fixed ends at the radialmember.
 6. The dynamic biometric mesh of claim 1 wherein the catenariesare elastic having a defined stretch under tension.
 7. The dynamicbiometric mesh of claim 6 wherein the radial members are elastic havinga defined stretch under tension.
 8. The dynamic biometric mesh of claim1 wherein the mesh is conformable about a convex curvature.
 9. Thedynamic biometric mesh of claim 8 wherein the outer perimeter has aplurality of attachment or anchoring points to attach the mesh totissue.
 10. The dynamic biometric mesh of claim 9 wherein the mesh canbe stretched to the attachment points to pre-tension the mesh along theattachments.
 11. The dynamic biometric mesh of claim 10 wherein thepre-tensioning of the mesh places a tension on the catenaries andwherein the catenaries achieve a tensioned equilibrium after beingaffixed.
 12. The dynamic biometric mesh of claim 11 wherein thecatenaries stretch under expansion or retract under contraction inrelation to the movement of the tissue to which the mesh is affixed. 13.The dynamic biometric mesh of claim 1 wherein the mesh has an asymmetricconfiguration having an upper hemisphere extending above the centralopening of increased elasticity or stretch and a lower hemisphere havinga reduced elasticity or stretch.
 14. The dynamic biometric mesh of claim13 wherein the lower hemisphere has a plurality of struts, each strutextending diagonally between adjacent catenaries and adjacent radialmembers.
 15. The dynamic biometric mesh of claim 14 wherein the strutsare attached to intersections of a respective catenary and radialmembers.
 16. The dynamic biometric mesh of claim 12 wherein at least anupper portion or hemisphere of the mesh can expand under tension atleast to 150% from its as formed unattached structure.
 17. The dynamicbiometric mesh of claim 16 wherein the radial members and the catenarieshave the same elasticity.
 18. The dynamic biometric mesh of claim 14wherein the struts, radial members and catenaries have the sameelasticity.
 19. The dynamic biometric mesh of claim 14 wherein thestruts of the lower hemisphere are positioned diagonally at eachintersection and can be selectively removed by cutting one or morestruts to tune the structure of the mesh to accommodate the tissue towhich the mesh is attached.
 20. The dynamic biometric mesh of claim 1wherein one or more of the plurality of catenaries is formed as a shelfhaving a width (w) and a length (l) creating top and bottom surfaceareas to affix biological materials, chemicals or pharmaceuticals toenhance tissue integration.
 21. The dynamic biometric mesh of claim 1wherein the mesh is formed by weaving monofilaments in a multi-plyconfiguration.
 22. The dynamic biometric mesh of claim 21 wherein themesh is a three ply configuration.
 23. The dynamic biometric mesh ofclaim 1 wherein the mesh redirects forces from lateral tension intorostral-caudal alignment to direct reconstitution and normalize tissuerepair.
 24. The dynamic biometric mesh of claim 1 wherein the mesh is amulti-tiered structure having two or more connected layers of mesh. 25.The dynamic biometric mesh of claim 1 wherein the mesh distributestension across the catenaries and radial members to dissipate dynamicforces at the anchoring points.
 26. The dynamic biometric mesh of claim1 wherein the mesh is configured for attachment to an abdominal wall foruse in repair of abdominal wall hernias.
 27. The dynamic biometric meshof claim 1 wherein the mesh is configured to provide dynamicstabilization and support of breast tissue.
 28. The dynamic biometricmesh of claim 1 wherein the mesh is degradably defined by the materialcomposition to be selectively absorbed or biologically integrated intothe tissue to which it is attached.
 29. The dynamic biometric mesh ofclaim 1 wherein the mesh is formed using one or more techniques such ascast, printed, corrugated, embossed, extruded, die cut, welded, laseretched, laser modified tissue mimetic biodynamic or any combinationthereof.
 30. The dynamic biometric mesh of claim 29 wherein the mesh hasrandom or preferred surface orientation and roughness.
 31. The dynamicbiometric mesh of claim 1 wherein intrinsic cell instruction propertiesare engineered into fibers which make up the catenaries and radialmembers using laser etching, the cell instruction properties of the meshpromotes incorporation of the mesh into surrounding tissues by promotingtissue ingrowth.
 32. The dynamic biometric mesh of claim 1 wherein metalsalts are incorporated into fiber of the catenaries and radial membersto act as competitive inhibitors to mediators of inflammatory response.33. The dynamic biometric mesh of claim 32 wherein these metal saltsinclude titanium dioxide as a competitive inhibitor of metalloproteasemediators of the inflammatory response.
 34. The dynamic biometric meshof claim 1 wherein the mesh is conditioned with autologous mesenchymalstem cells (MSCs) derived from processed adipose tissue, and consistentwith the stromal vascular fraction (SVF).
 35. The dynamic biometric meshof claim 34 wherein the mesh is conditioned with the MSCs in abioreactor in advance of insertion into the hernia defect.
 36. Thedynamic biometric mesh of claim 35 wherein the mesh has a matrix toenhance cell attachment, stimulate differentiation and accentuate forcetransduction in alignment of the cell orientation.
 37. The dynamicbiometric mesh of claim 36 wherein the mesh is a biosynthetic compositestructure customized to the subject and accelerates incorporation intoadjacent tissues.
 38. The dynamic biometric mesh of claim 1 wherein themesh is manufactured using a 3-D printing technology.
 39. The dynamicbiometric mesh of claim 38 wherein the mesh is made on demand and toprecisely match the hernia defect in the subject based on non-invasivemeasurements including physical examination.
 40. The dynamic biometricmesh of claim 1 wherein the mesh is formed as a broad platform ofuniform isotropic distributed radial members and catenaries or strutsformed by either printed, laser cut, die cut, embossed, sprayed onsuitable differential electrodes to align charge, or other means. 41.The dynamic biometric mesh of claim 40 wherein the catenaries, radialmembers or struts are over sprayed with collagen, PGLA, PCL,Poly-imides, or other bio-absorbable polymers.
 42. The dynamic biometricmesh of claim 1 wherein the mesh emulates zoomorphic design,specifically that of a spider web, and is intended to possess an openarchitecture thus reducing infection and inflammation.
 43. The dynamicbiometric mesh of claim 42 wherein the stress or elongationcharacteristics of the mesh are suited to accommodating the cyclicalload bearing properties of the ventral abdominal wall and theinterstices of the mesh are smaller than 12 mm or less.
 44. The dynamicbiometric mesh of claim 1 wherein the mesh incorporates one or morefeatures in cross section of a woody stem, of a plant branchinginterface, demonstrates regular and randomized cells, Fibonacci andordered arrays, varying diameters and regular, ordered arrays of innercells any of which imparting structural tension to lateral distortionwithout imposing material stiffness.
 45. The dynamic biometric mesh ofclaim 1 wherein the tensile strength of the catenaries or radial membersare formed as fibers having a tensile strength in the range of 50 to 150N/m.
 46. The dynamic biometric mesh of claim 45 wherein the tensilestrength of the catenaries or radial members are formed as fibers havinga tensile strength of 100 N/m.
 47. The dynamic biometric mesh of claim 1wherein the catenaries and radial members have a fiber diameter of 0.2mm or greater.
 48. The dynamic biometric mesh of claim 47 wherein thecatenaries and radial members have a fiber diameter of 0.26 mm.
 49. Thedynamic biometric mesh of claim 45 wherein the Young's modulus ofcomponent fibers is 34 GPa or greater.
 50. The dynamic biometric mesh ofclaim 9 wherein the suture pull out strength is at least 5.5 kg at theouter perimeter of the mesh.